JP2020010880A - Non-invasive sugar in blood meter - Google Patents
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- 239000008280 blood Substances 0.000 title claims abstract description 82
- 210000004369 blood Anatomy 0.000 title claims abstract description 82
- 235000000346 sugar Nutrition 0.000 title claims abstract description 52
- 238000005259 measurement Methods 0.000 claims abstract description 28
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 claims description 63
- 239000008103 glucose Substances 0.000 claims description 63
- 238000010521 absorption reaction Methods 0.000 claims description 28
- 210000003722 extracellular fluid Anatomy 0.000 claims description 9
- 150000008163 sugars Chemical class 0.000 claims 1
- 238000010586 diagram Methods 0.000 abstract description 6
- 230000005540 biological transmission Effects 0.000 abstract description 5
- 230000007423 decrease Effects 0.000 abstract description 4
- 230000004907 flux Effects 0.000 abstract description 2
- 230000010355 oscillation Effects 0.000 abstract description 2
- 230000031700 light absorption Effects 0.000 abstract 1
- 210000003811 finger Anatomy 0.000 description 11
- 210000003491 skin Anatomy 0.000 description 10
- 230000008033 biological extinction Effects 0.000 description 6
- 235000013305 food Nutrition 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 239000007788 liquid Substances 0.000 description 3
- 230000003287 optical effect Effects 0.000 description 3
- 238000002310 reflectometry Methods 0.000 description 3
- 210000003813 thumb Anatomy 0.000 description 3
- 238000010241 blood sampling Methods 0.000 description 2
- 230000001419 dependent effect Effects 0.000 description 2
- 230000005684 electric field Effects 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 238000002834 transmittance Methods 0.000 description 2
- 238000002835 absorbance Methods 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 238000002788 crimping Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000009792 diffusion process Methods 0.000 description 1
- 210000000624 ear auricle Anatomy 0.000 description 1
- 235000013399 edible fruits Nutrition 0.000 description 1
- 210000002615 epidermis Anatomy 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000005457 optimization Methods 0.000 description 1
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- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
Description
光を生体に当て生体 内部を計測する 応用生体光計測分野。 Applied biological light measurement field that measures the inside of a living body by applying light to the living body.
従来の光を利用した非侵襲血糖計のアイデアは 糖分子の吸光度に注目したものであり、典型的な例は 図1のように指に入射光I0を照射し、透過光Itを計測するものである。
すると（１）が成り立つ。
The idea of a conventional non-invasive blood glucose meter using light focuses on the absorbance of sugar molecules, and a typical example is to irradiate a finger with incident light I0 and measure transmitted light It as shown in Fig. 1. It is.
Then, (1) holds.
意図するところは Itを計測し（１）からαを算出するものである。
ところが 実用的には 全て失敗している。理由はαｄが 大きすぎ 或はItの信号レベルが小さすぎ 現在の検出器では α検知に至らない ということである。
図2は従来例である。手指・耳朶の透過を狙ったものである。出典は下記の非特許文献である。
これも失敗例である。
そこで 従来の透過例を鑑みて 出来るだけｄを小さくする目的で図3 のようなアイデアが考案されている。
図3のように入射光I０を指の肉厚面に接するが如く斜入射する。透過光Itは 指の肉厚面に接するが如く斜め拡散出射する。これはｄの出来るだけ小さいことを狙って 指の表皮に斜入射、斜拡散出射の構成になっている。
この場合 拡散反射光（＝透過光＝皮膚に入り 再び皮膚から外の空気域に出る光）を計測している。この場合の 最近 出願公開されている例を下記の特許文献に示す。
その図４のなかで読み取れるように斜光線入射の工夫がされているが 実用的には 失敗している。
それは ｄが小さくとれなく トータル 測定精度に問題があると考えられることである。
The intention is to measure It and calculate α from (1).
However, practically everything has failed. The reason is that αd is too large or the signal level of It is too small and the current detector does not lead to α detection.
FIG. 2 shows a conventional example. It aims to transmit through fingers and earlobes. The source is the following non-patent literature.
This is also a failure.
Therefore, an idea as shown in Fig. 3 has been devised for the purpose of making d as small as possible in view of the conventional transmission example.
As shown in FIG. 3, the incident light I0 is obliquely incident so as to be in contact with the thick surface of the finger. The transmitted light It is obliquely diffused and emitted as if it were in contact with the thick surface of the finger. This is a configuration of oblique incidence and oblique diffusion emission to the skin of the finger aiming at d as small as possible.
In this case, the diffuse reflected light (= transmitted light = light that enters the skin and exits the skin to the outside air area) is measured. The following patent documents show examples of recently published applications in this case.
The oblique light beam is devised so that it can be read in Fig. 4, but it has failed in practice.
It is considered that d cannot be small and there is a problem in total measurement accuracy.
M．Noda et al．：Diabetologia,35(suppl),ｐＡ204(1994)
近赤外センシング技術 （株）サイエンス フォーラム)
Near-infrared sensing technology (Science Forum)
従来の光を使った 非侵襲血糖計は 皮膚内に入った透過光が再び空気域に出ていく透過光 或は 拡散反射光には注目していた。それは（１）式によって表されるα・ｄが大きく 結果Itの信号レベルが小さく測定精度に問題があった。
それに対して本発明は 本発明は、皮膚内に入った透過光が再び空気域に出ていく透過光
或は 拡散反射光には注目していなく、空気域と媒体（皮膚）の境界面における反射率変化と人体の間質液の糖濃度に注目する。
本発明は 人体の間質液の糖濃度と血中の糖濃度が近似していることを利用して 皮膚表面の 反射率の変化から皮膚内の間質液の糖濃度を計測して 血中の糖濃度を算定する非侵襲血糖測定装置である。
Conventional non-invasive blood glucose meters using light have focused on transmitted light or diffuse reflected light where transmitted light that has entered the skin returns to the air space again. That is, α · d expressed by the equation (1) is large, and as a result, the signal level of It is small, and there is a problem in measurement accuracy.
On the other hand, the present invention does not focus on the transmitted light or the diffusely reflected light in which the transmitted light that has entered the skin returns to the air region, and does not focus on the interface between the air region and the medium (skin). Attention is paid to the reflectance change and the sugar concentration of the interstitial fluid of the human body.
The present invention utilizes the fact that the sugar concentration in the interstitial fluid of the human body and the sugar concentration in the blood are close to each other, and measures the sugar concentration of the interstitial fluid in the skin from the change in the reflectance of the skin surface. This is a non-invasive blood glucose measuring device for calculating the glucose concentration of the blood sugar.
人体の皮膚表面に光が入射し 反射し 反射率測定の様子は例えば 図６に示す。指に必要な光が入射し、正反射角で光を受光素子Dで受け 電気信号により 人体の間質液の糖濃度を反映した複素数屈折率の境界面の反射率測定を行い 血中糖濃度を非侵襲でMで表示する。
次に反射率測定が 糖濃度にいかに関係するか説明する。
人体の間質液の糖濃度は 血中糖濃度と近似しており、間質液の糖濃度が反射率測定で求め得ることを示す。
透過率計測ではないことがポイントである。
図５は air空気とa-b面で接している 複素数屈折率Nの人体の間質液媒体を模式的に示したものである。
図５のように 入射角：Ψ0、反射角：Ψ0。反射率は次式で表される。
例えば インターネットHP
home.sato-gallery.com/hikaribussei/chap3.html
より
Light is incident on the skin surface of the human body and is reflected. The state of the reflectance measurement is shown in FIG. 6, for example. The required light is incident on the finger, the light is received by the light receiving element D at the specular reflection angle, and the reflectance of the complex refractive index interface reflecting the sugar concentration of the interstitial fluid of the human body is measured by an electrical signal. Is displayed in M non-invasively.
Next, we explain how reflectance measurement relates to sugar concentration.
The sugar concentration in the interstitial fluid of the human body is close to the blood sugar concentration, indicating that the sugar concentration in the interstitial fluid can be determined by reflectance measurement.
The point is that it is not transmittance measurement.
FIG. 5 schematically shows a human interstitial liquid medium having a complex refractive index N in contact with air at the ab plane.
As shown in FIG. 5, the incident angle: Ψ0 and the reflection angle: Ψ0. The reflectance is represented by the following equation.
For example, Internet HP
home.sato-gallery.com/hikaribussei/chap3.html
Than
ここで
N＝n＋ｉK
N：複素数屈折率
n：実部屈折率
K：K消衰係数：α＝４πK/λ：波長依存の吸収係数：濃度に比例
このKが求めたい血中糖濃度である。
Rp：入射光線、反射光線に垂直（図5の紙面上）の電界強度の反射率、
Rs：入射光線、反射光線に垂直（図5の紙面垂直）の電界強度の反射率
定性的に（3.11）を理解するために
Ψ0＝０
垂直入射、垂直反射の場合をかんがえる。
すると(3.11) は
here
N = n + iK
N: complex number refractive index
n: Real part refractive index
K: K extinction coefficient: α = 4πK / λ: wavelength-dependent absorption coefficient: proportional to concentration K is the blood glucose concentration to be determined.
Rp: reflectivity of electric field strength perpendicular to the incident light and reflected light (on the paper of Fig. 5),
Rs: reflectivity of electric field intensity perpendicular to the incident light and reflected light (perpendicular to the plane of FIG. 5) 50 = 0 to understand qualitatively (3.11)
Consider the case of normal incidence and normal reflection.
Then (3.11) is
Rp＝Rsとなり、Rと置き直すと
Rp = Rs, and replace it with R
K消衰係数：α＝４πｋ/λ：波長依存の吸収係数：濃度に比例：間質液糖度に比例：血中糖度に比例 K extinction coefficient: α = 4πk / λ: wavelength-dependent absorption coefficient: proportional to concentration: proportional to interstitial liquid sugar: proportional to blood sugar
（２）は Rの計測からnをパラメーターにして Kが分かることをしめしている。nは人種、性別、年齢、職種、食物などによって変わることもあり得る。
そこで 実用上は 血中糖濃度の計測範囲を前もって網羅する必要があり、実用上問題ない 条件に従った生体区分によるRとKの対応表を用意し、計測したRから Kを求めることができる。
或は 表ではなく RとKの関係を 属性に従って関数近似でも問題ない。
事前の計測で 採血方式により 血糖値とKの関係が値付けされる。
次に nの値によらず RとKの関係が成り立つことを示す。
(2) shows that K is known from the measurement of R using n as a parameter. n can vary depending on race, gender, age, occupation, food, etc.
Therefore, in practice, it is necessary to cover the measurement range of blood glucose concentration in advance, and it is possible to prepare a correspondence table of R and K by biological classification according to conditions that are not practically problematic, and obtain K from the measured R. .
Or there is no problem with function approximation based on the attribute of R and K instead of the table.
Prior measurement determines the relationship between blood glucose and K by blood sampling method.
Next, we show that the relationship between R and K holds regardless of the value of n.
（７）の示唆するところはR0を前もって計測し （２）の複素数Nの実数部nによらず計測時にはRから血中糖濃度Kを求めることができることをしめしている。
R0の意味するところは 血中糖度（吸収係数）の波長依存性がゼロの場合の実数部屈折率に対応する反射率であり、糖分子を含めた他分子の総合実数部屈折率に対応する。
吸収波長域Kが糖分子のみとすると 吸収域近傍のR０は吸収域の総合実数屈折に対応している。
ここではnの波長に対する変化はKより小さいことを応用している。
また （２）からnを消去する別方法は 波長をパラメーターにしてRとKの独立式を実験的に複数求めることでも得られる。
血中糖の吸光係数（消衰係数）の波長依存性は8.5μ〜10.0μ（Frontiers Med.Biol.Enbng,Vol.9,Ｎｏ．２,pp.137−153（1999））と示されている。
これにより Rの計測には8.5μ〜10.0μの波長を R0の計測には8.5μ未満か10.0より長い波長を用いる。重要なことはR0が分かれば Rから総合実数率屈折率を消去した Kを求め得るということである。
（５によるR0とnの関係は厳密には 人種、性別、年齢、職種、食物などによって変わることもあり得る。
そこで 実用上は 血中糖濃度の計測範囲を前もって網羅する必要があり、実用上問題ない nの生体区分によるRとKの対応表を用意し、計測したRから Kを求めることもきる。或は 表ではなく RとKの関係を関数近似でも問題ない。
事前の計測で 採血方式により 血糖値とKの関係が値付けされる。
The suggestion of (7) indicates that R0 is measured in advance, and the blood glucose concentration K can be obtained from R at the time of measurement regardless of the real part n of the complex number N in (2).
The meaning of R0 is the reflectance corresponding to the real part refractive index when the wavelength dependence of blood sugar content (absorption coefficient) is zero, and corresponds to the total real part refractive index of other molecules including sugar molecules. .
If the absorption wavelength region K is only sugar molecules, R0 near the absorption region corresponds to the total real number refraction of the absorption region.
Here, it is applied that the change with respect to the wavelength of n is smaller than K.
Another method for eliminating n from (2) can also be obtained by experimentally obtaining a plurality of independent equations for R and K using the wavelength as a parameter.
The wavelength dependence of the extinction coefficient (extinction coefficient) of blood sugar is indicated as 8.5 μ to 10.0 μ (Frontiers Med. Biol. Enbng, Vol. 9, No. 2, pp. 137-153 (1999)). I have.
Thus, a wavelength of 8.5μ to 10.0μ is used for measuring R, and a wavelength of less than 8.5μ or longer than 10.0 is used for measuring R0. The important thing is that if R0 is known, K can be obtained from R by eliminating the total real index.
(Strictly speaking, the relationship between R0 and n according to 5 can vary depending on race, gender, age, occupation, food, etc.)
Therefore, in practice, it is necessary to cover the measurement range of blood glucose concentration in advance, and it is possible to prepare a correspondence table of R and K according to n biological categories, which is not a problem in practical use, and obtain K from the measured R. Or it is not a problem to use a function approximation for the relationship between R and K instead of a table.
Prior measurement determines the relationship between blood glucose and K by blood sampling method.
以上が基本的な本発明の理論骨子である。
しかし 実際にはRは RsとRsとは厳密には異なるRpの混在であり 境界面の微細構造も反射率に影響を与えるので 反射率Ｒと血中糖度（Ｋ比例）の対応データは 必要十分な実験による実用上問題ない領域（年齢分布、人種分布、男女差、食物などを考慮した）、の Ｒ、Ｒ0 、Ｋ データ或はR、n、Kデータでないといけない。
さらに被測定表面に等価的に透過フィルターに相当する、例えば 汚れとかが カバーされている場合を考慮する。このフィルターの透過因子をXとする。入射と反射の2重に因子がかかる。
すると（２）、（５）は
The above is the basic theory of the present invention.
However, in fact, R is a mixture of Rs and Rp, which is strictly different from Rs, and the fine structure of the boundary surface also affects the reflectance. Therefore, the corresponding data of the reflectance R and the blood sugar content (K proportional) are necessary and sufficient. It must be R, R0, K data or R, n, K data in a practically acceptable region (considering age distribution, race distribution, gender difference, food, etc.) by a simple experiment.
In addition, consider the case where the surface to be measured is covered with a filter equivalent to a transmission filter, for example, dirt. Let X be the transmission factor of this filter. There is a factor in the double of incident and reflected.
Then (2) and (5)
R’はXを踏まえた吸収波長域の反射 であり、R0’は吸収波長域外の反射率である。
（９）からXも性別、年齢、職種、人種、食物などによる区分けして使用することも可能であり、予め測定して生体のR’、X、n、K区分表をつくり R‘からK値を対応表により求めることも可能である。
（９）（１０）は未知数X、nの２個であり、独立式が２個であり（Kの値は独立に選ぶことができ ２個以上の独立式が得られる）、X、nを求めることができる。
Xが求まれば（９）（１０）からR,R0がもとまり（２）、（５）の展開が可能である。
この場合の生体区分にはXのデータを加味した生体区分表からR0’、R’からKを求めることも可能である。また光入射角はゼロが理想であるが ３５度未満の入射角であれば実用に供すると考える。
R 'is the reflection in the absorption wavelength range based on X, and R0' is the reflectance outside the absorption wavelength range.
From (9), it is also possible to use X by classifying it by gender, age, occupation, race, food, etc., and measure it in advance to create a R ', X, n, K classification table for the living body, and from R' It is also possible to determine the K value from a correspondence table.
(9) and (10) are two unknowns X and n, and there are two independent equations (the value of K can be independently selected and two or more independent equations are obtained). You can ask.
If X is obtained, R and R0 can be obtained from (9) and (10), and (2) and (5) can be expanded.
In this case, R0 'and K from R' can be obtained from the biological classification table in which the data of X is added to the biological classification. Although the ideal light incident angle is zero, it is considered that the light incident angle is practical if the incident angle is less than 35 degrees.
本発明例として （２） 或は（９）を応用した 血中糖の吸収波長8.5μ〜10.0μのいずれかの波長を用いて反射率を計測しCO2ガスレーザーを使用し光入射角ゼロ近傍の35度未満
の入射角を持つ 生体区分表をもつ血中糖濃度を計測する非侵襲血糖計である。
As an example of the present invention, applying (2) or (9), the reflectance is measured using any one of the absorption wavelengths of blood sugar of 8.5 to 10.0 μm, and a CO2 gas laser is used, and the light incident angle is near zero. This is a non-invasive blood glucose meter that measures blood glucose concentration with a biological classification table having an incident angle of less than 35 degrees.
本発明の別例として （５）或は（１０）を応用した 血中糖の吸収波長8.5μ〜10.0μのいずれかの波長を用いて反射率を計測し、血中 糖の吸収無しの波長として8.５μに近い
8.5μより短波長の波長を用いるか 10.0μに近い 10.0μより長波長を用いて CO2ガスレーザーを使用し入射角ゼロ近傍の35度未満の入射角を持つ 血中糖濃度を計測する非侵襲血糖計である。
図６は 本発明の別例の主要な構成ブロック図の例である。
LはCO2ガスレーザー光源であり、波長9.2〜10.8μmの複数輝線状の光束径が数ｍｍ程度の発振周波数１ＫＨＺ〜100ＫＨＺで射出される。出射光のレベルはＭｓの分岐ミラーにより受光素子Ｍｒにより監視する。LはCO2レーザー光源に限定するものではない。
別途光パラメトリック発振器であってもよい。FはLから必要な波長を取り出す装置である。
血中糖の吸光係数（消衰係数）の波長依存性は8.5μ〜10.0μ（Frontiers ed.Biol.Enbng,Vol.9,Ｎｏ．２,pp.137−153（1999））と示されている。
必要な波長は 例えば、図7に示すように 9.6μ、10.2μ、bl遮光の３種を選ぶ。
rtb回転板に光通過窓をもたせ9.6μの回折フィルター、10.2μの回折フィルター、遮光の各選択が巡回する構成にする。
rtb回転のサイクルは受光素子のレスポンにあわせる。熱電対の場合は概１Ｈｚにする。これらの回折フィルターは光量レベルの調整もＮＤフィルターなどで行う。
これら回折フィルターは干渉フィルターであってもよい。あるいは回転板は 横スライドの往復機構を持つ手段であってもよい。
あるいは 電磁気か音響による回折格子の定数を変化さす 不動型の光学フィルターであってもよい。或は9.6μと遮光の２種であってもよい。
図７のLaserはレーザー光である。図６のＭ1、Ｍ2、Ｍ3 は 光路を変更するためのミラーで１枚〜複数枚使う。
ＦＸは被測定物、例えば図８に示すような指の固定装置であり 測定時間内固定される。ＦＸは被測定物、例えば図８に示すような指の固定装置であり 測定時間内固定される。例えば親指の第一関節から指先までの肉厚表皮を使う場合、図８に示すように 入射光穴に 抑え板で 第一関節から指先が動かないように 固定する。抑え板は バネ性の金属で方側は固定されており 親指を挿入して他の側に 例えば 図のように回転ネジで圧迫固
定する。
親指を 固定し易くするため 固定板に 指肉厚の堀の形状を設け、略中央に入射光穴をあける。この抑え板は くりかえし使用が可能なテープで少なくとも片側で例えばマジック固定であってもよい。あるいは洗濯バサミ状の 指抑えであってもよい。
また この固定装置は反射光Ｉｒが最大になるように 自動的或は手動により機構が３次元的に動かし得る。メカニズムは図示していないが 組み立てロボットなどの公知手段を使う。
自動化のメカニズムの原理は 例えば図9にしめす。
少なくともnn法線方向に動くstm直進手段（第一手段）と入射点を中心に紙面垂直の回転軸（rt1回転１）を有する手段（第二手段）と入射点を中心に 紙面上の法線直角の回転軸（rt2回転２）を有する手段（第三手段）をもち、これら手段を用いて 自動 あるいは手動で最適位置にfxb固定治具とD受光素子を固定する。
最適化の方法は 例えば第一手段の微小変動でIr反射光の増減をみながら局部最大値をもとめ、次に第二手段の微小変動でIrの増減をみながら局部最大値をもとめ、次に第三手段の微小変動でIrの増減をみながら局部最大値をもとめ て位置を固定する。これらを自動
あるいは手動でおこなう。
pbは圧着板である。
Ｄは受光素子である。
入射角と反射角が出来るだけ０度になるようにし かつ 受光量を多くする。そのために受光素子の縁近くを入射光が通り、受光部と被測定部を近接さす。
受光素子は9.2μ〜10.8μに感度があり、高感度のものほどよい。
強制冷却型素子でもいいし あるいは 常温タイプの熱電対でもよい。
Ｍは必要な表示を例えば 血糖濃度 時刻 時間などを 算出 表示するもので、又 予め必要な 生体区分ごとのRとKの対応表とか 測定ごとの記憶とか、測定ごとの出力などをする装置である。
9.6μ波長については
Ir＝反射率R×I9・・・・・（１１）
I9入射光 はＭｒで計測し、IrはＤで測定する。
（１１）によりＲが計測される。
遮光については遮光によりノイズレベルを測定する。
夫々の計測値から ノイズレベルを引いた値をIr、I9とする。
10.2μについては 糖吸収外の近傍波長である。
As another example of the present invention, the reflectivity is measured using any one of the absorption wavelengths of blood sugar of 8.5 μ to 10.0 μ to which (5) or (10) is applied, and the wavelength without absorption of blood sugar is measured. Close to 8.5μ
Use a wavelength shorter than 8.5μ or a wavelength close to 10.0μ and a wavelength longer than 10.0μ and use a CO2 gas laser to measure the blood glucose concentration with an incident angle of less than 35 ° near zero incident angle using a CO2 gas laser It is a blood glucose meter.
FIG. 6 is an example of a main configuration block diagram of another example of the present invention.
L is a CO2 gas laser light source, which is emitted at an oscillation frequency of 1 KHZ to 100 KHZ with a luminous flux diameter of a plurality of bright lines having a wavelength of 9.2 to 10.8 μm of about several mm. The level of the emitted light is monitored by the light receiving element Mr using the Ms branch mirror. L is not limited to a CO2 laser light source.
An optical parametric oscillator may be separately provided. F is a device for extracting a required wavelength from L.
The wavelength dependence of the extinction coefficient (extinction coefficient) of blood sugar is indicated as 8.5 μ to 10.0 μ (Frontiers ed. Biol. Enbng, Vol. 9, No. 2, pp. 137-153 (1999)). I have.
As the required wavelength, for example, as shown in FIG. 7, three kinds of 9.6 μm, 10.2 μm, and bl light shielding are selected.
The rtb rotating plate is provided with a light passing window, and the configuration is such that the selection of a 9.6 μ diffraction filter, a 10.2 μ diffraction filter, and light shielding is repeated.
The cycle of the rtb rotation is adjusted to the response of the light receiving element. In the case of a thermocouple, the frequency is approximately 1 Hz. These diffraction filters also adjust the light amount level using an ND filter or the like.
These diffraction filters may be interference filters. Alternatively, the rotating plate may be a means having a reciprocating mechanism of a horizontal slide.
Alternatively, it may be an immovable optical filter that changes the constant of the diffraction grating by electromagnetic or acoustic. Alternatively, two types, 9.6 μ and light shielding, may be used.
Laser in FIG. 7 is a laser beam. M1, M2, and M3 in FIG. 6 are mirrors for changing the optical path, and one or more mirrors are used.
FX is a device for fixing an object to be measured, for example, a finger as shown in FIG. 8, and is fixed within the measurement time. FX is a device for fixing an object to be measured, for example, a finger as shown in FIG. 8, and is fixed within the measurement time. For example, when using a thick skin from the first joint of the thumb to the fingertip, as shown in Fig. 8, fix the fingertip from the first joint with a holding plate in the incident light hole. The holding plate is fixed with spring metal on one side, and the thumb is inserted and the other side is pressed and fixed with a rotating screw as shown in the figure.
In order to make it easier to fix the thumb, a thick moat is formed on the fixing plate, and an incident light hole is made at the approximate center. This holding plate may be a tape that can be used repeatedly, for example, magically fixed on at least one side. Alternatively, it may be a finger clamp shaped like a clothespin.
In addition, the fixing device can automatically or manually move the mechanism three-dimensionally so that the reflected light Ir is maximized. Although the mechanism is not shown, a known means such as an assembly robot is used.
The principle of the automation mechanism is shown in Fig. 9, for example.
A stm linear moving means (first means) moving at least in the nn normal direction, a means (second means) having a rotation axis (rt1 rotation 1) perpendicular to the paper centering on the incident point, and a normal on the paper surface centering on the incident point It has means (third means) having a right-angle rotation axis (rt2 rotation 2), and automatically or manually fixes the fxb fixing jig and the D light receiving element at the optimum position using these means.
The optimization method is, for example, to obtain the local maximum value while observing the increase and decrease of the Ir reflected light by the minute fluctuation of the first means, and then to obtain the local maximum value while observing the increase and decrease of Ir by the minute fluctuation of the second means, The position is fixed by obtaining the local maximum value while observing the increase and decrease of Ir with the slight fluctuation of the third means. Perform these automatically or manually.
pb is a crimp plate.
D is a light receiving element.
The incident angle and the reflection angle are set to 0 ° as much as possible, and the amount of received light is increased. For this purpose, the incident light passes near the edge of the light receiving element, and the light receiving section and the measured section are brought close to each other.
The light receiving element has a sensitivity of 9.2 μ to 10.8 μ, and the higher the sensitivity, the better.
A forced cooling type element or a room temperature type thermocouple may be used.
M is a device for calculating and displaying necessary displays, for example, blood glucose concentration, time, time, and the like, and for performing a necessary correspondence table of R and K for each living body division, storing for each measurement, and outputting for each measurement. .
For 9.6μ wavelength
Ir = reflectance R × I9 (11)
I9 incident light is measured by Mr, and Ir is measured by D.
R is measured by (11).
As for the light shielding, the noise level is measured by the light shielding.
The values obtained by subtracting the noise level from the respective measured values are Ir and I9.
For 10.2μ, it is a near wavelength outside the sugar absorption.
K＝0
Iｒ0 ＝R0×I0 ・・・・・（１２）
I0はＭｒで計測し、Iｒ0はＤで測定する。
（１２）によりＲ０が計測される。
K = 0
Ir0 = R0 × I0 (12)
I0 is measured by Mr, and Ir0 is measured by D.
R0 is measured by (12).
この場合も遮光時のノイズレベルを計測する。
このノイズ値を 夫々の入射値、反射値 から引く。
その値がIｒ0、I0であり（１２）からＲ0を求める。
更に（3.11）は人体の血中糖度だけに適用され得るものではなく、同様の応用は植物の果物などの生体糖度計測にも適用できる。
被計測体を植物の生体に変えればよい。
本発明は 具体例として糖分子に注目したものであるが、非糖分子であっても（3.11）で示唆される分子が吸収波長をもち液中に混在する場合の分子量計測にも適用され得る。
Also in this case, the noise level at the time of shading is measured.
This noise value is subtracted from each incident value and reflection value.
The values are Ir0 and I0, and R0 is obtained from (12).
Furthermore, (3.11) cannot be applied only to the sugar content in the blood of the human body, and the same application can be applied to the measurement of the sugar content of a living body such as a fruit of a plant.
What is necessary is just to change an object to be measured to a living body of a plant.
Although the present invention focuses on sugar molecules as a specific example, even non-sugar molecules can be applied to measurement of molecular weight when molecules suggested in (3.11) have an absorption wavelength and are mixed in a liquid. .
透過光の血中糖度計測の代わり 境界面の反射率を計測して非侵襲血中糖度計測をする。
Non-invasive blood glucose measurement is performed by measuring the reflectance of the interface instead of measuring the transmitted light blood glucose.
図６に示す必要な手段から成る。 It consists of the necessary means shown in FIG.
I0:入射光、It：透過光、air：空気、N：複素数屈折率、n：実部屈折率
K：虚数部屈折率＝消耗係数（∝血中糖濃度）、Mｓ：分岐ミラー
L：レーザー光源、F：フィルター、Mr：受光部、M1：ミラー
M2：ミラー、M3：ミラー、Fx：固定装置、D：受光部、M：表示演算装置
Laser：レーザー光、rtb：回転板、bl：遮光板、9.6μ：9.6μレーザー
10.2μ：10.2μレーザー、rt：回転、rta：回転軸、stm：直進移動、
fxb：固定板、rt1：回転１、rt2：回転２、pb：圧着板、D：受光部、
I9：入射光、nn：法線、Ir：反射光
I0: incident light, It: transmitted light, air: air, N: complex number refractive index, n: real part refractive index
K: Imaginary part refractive index = consumption coefficient (∝blood sugar concentration), Ms: branching mirror
L: Laser light source, F: Filter, Mr: Receiver, M1: Mirror
M2: Mirror, M3: Mirror, Fx: Fixed device, D: Light receiving unit, M: Display operation device
Laser: Laser light, rtb: Rotating plate, bl: Light shielding plate, 9.6μ: 9.6μ laser
10.2μ: 10.2μ laser, rt: rotation, rta: rotation axis, stm: linear movement,
fxb: fixed plate, rt1:
I9: incident light, nn: normal, Ir: reflected light
Claims (19)
10.0μより長波長を使用するCO2ガスレーザーを使用する請求項２の血中糖濃度を計測する非侵襲血糖計。 Measure the reflectance using any of the absorption wavelengths of blood sugar 8.5μ to 10.0μ, and use a wavelength shorter than 8.5μ close to 8.5μ as the wavelength without absorption of blood sugar 10.0μ Close to
3. The noninvasive blood glucose meter for measuring blood glucose concentration according to claim 2, wherein a CO2 gas laser using a wavelength longer than 10.0 μm is used.
測する非侵襲血糖計。 8. The blood according to claim 7, wherein the reflectance is measured by using any one of 9.3 μ, 9.4 μ, 9.5 μ, and 9.6 μ of the absorption wavelength of blood sugar, and each diffraction filter and a light shielding plate are attached to the rotating plate. A non-invasive blood glucose meter that measures glucose concentration.
測する非侵襲血糖計。 The blood glucose according to claim 13, wherein the reflectance is measured using any one of 9.3 μ, 9.4 μ, 9.5 μ or 9.6 μ of the absorption wavelength of blood sugar, and each diffraction filter and light shielding plate are attached to the rotating plate. A non-invasive blood glucose meter that measures glucose concentration.
非侵襲糖度計。 The sugar concentration in the interstitial fluid is measured by the reflectance measurement at the interface of the complex refractive index that reflects the sugar concentration of the interstitial fluid of the living body excluding the human body, which is measured at the specular reflection angle almost corresponding to the incident angle within 35 degrees. Non-invasive refractometer to measure.
波長を使用するCO2ガスレーザーを使用する請求項17の糖濃度を計測する非侵襲糖度計。 Measure the reflectance using any of the sugar absorption wavelengths 8.5μ to 10.0μ, and use a wavelength shorter than 8.5μ close to 8.5μ as the wavelength without sugar absorption or 10.0μ close to 10.0μ 18. The noninvasive saccharimeter for measuring a sugar concentration according to claim 17, wherein a CO2 gas laser using a longer wavelength is used.
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